Methods of making devices

ABSTRACT

The method of making devices is disclosed herein. More particularly, a method of manufacturing a device, comprises: vacuum depositing a device-forming metal onto an unpatterned, exterior surface of a generally cylindrical substrate to form a generally tubular, unpatterned crystalline metal film under at least one vacuum deposition process condition selected from at least one of chamber pressure, deposition pressure, and partial pressure of a process gas, said at least one process condition optimized to substantially eliminate formation of chemical and intra- and intergranular precipitates in the bulk material; and removing the deposited generally tubular, unpatterned crystalline metal film from the generally cylindrical substrate.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation application of co-pending U.S. patent application, Ser. No. 09/707,685, filed Nov. 7, 2000, and is related to U.S. patent application, Ser. No. 11/327,795, filed Jan. 6, 2006, herein incorporated by reference in their entireties.

BACKGROUND

The present invention relates generally to a method of making devices. More particularly, the present invention relates to manufacturing metal devices with radial or hoop strength and longitudinal flexibility, while maximizing fatigue life and corrosion resistance.

Metal devices utilize inherent material mechanical properties of the metal material. Typically, metal materials may rebound when a positive pressure is exerted against the material. Finally, shape-memory metals rely upon unique alloys that exhibit shape memory under certain thermal conditions. Conventional shape-memory is typically nickel-titanium alloys known generically as nitinol, which have a transition phase at or near normal body temperature, i.e., 37 degrees Centigrade.

One of the difficulties with many conventional metal designs arises due to the conflicting criteria between the desired properties of circumferential or hoop strength, longitudinal or column strength, longitudinal flexibility, fish-scaling of individual structural members, fatigue life, corrosion resistance, corrosion fatigue, hemodynamics, radioopacity and biocompatibility. Typically, metals that are designed to optimize for hoop strength typically sacrifice either column strength and/or longitudinal flexibility, while metals that are designed to optimize for column strength often compromise longitudinal flexibility and/or hoop strength.

Heretofore, however, the art has not devised a unibody metal structural element geometry which achieves a balance between hoop strength, column strength and longitudinal flexibility, circumferential strength or hoop strength of the stent, longitudinal strength or column strength, longitudinal flexibility, fish-scaling of individual structural members of the stent, fatigue life, corrosion resistance, corrosion fatigue, hemodynamics, radioopacity, biocompatibility

SUMMARY OF THE INVENTION

Provided herein are systems and methods for making devices. A method of manufacturing a metal, comprises: vacuum depositing a metal onto an unpatterned, exterior surface of a generally cylindrical substrate to form a generally tubular, unpatterned crystalline metal film under at least one vacuum deposition process condition selected from at least one of chamber pressure, deposition pressure, and partial pressure of a process gas, said at least one process condition optimized to minimize formation of chemical and intra- and intergranular precipitates in the bulk material; defining the plurality of first and second structural elements in the unpatterned metal film; and removing the first and second structural elements from the generally cylindrical substrate.

A method of manufacturing a device, comprises: vacuum depositing nickel and titanium onto an exterior surface of a generally cylindrical substrate to form a deposited generally tubular, crystalline nickel-titanium shape memory film having no less than about 51.5 atomic percent nickel, the vacuum deposition occurring under at least one vacuum deposition process condition selected from at least one of chamber pressure, deposition pressure, and partial pressure of a process gas, said at least one process condition optimized to minimize formation of inter- and intra-granular precipitates in the bulk material of the nickel-titanium crystalline film; and removing the deposited generally tubular, crystalline nickel-titanium shape memory film from the generally cylindrical substrate.

A method of manufacturing a device, comprises: vacuum depositing a device-forming metal onto an unpatterned, exterior surface of a generally cylindrical substrate to form a generally tubular, unpatterned crystalline metal film under at least one vacuum deposition process condition selected from at least one of chamber pressure, deposition pressure, and partial pressure of a process gas, said at least one process condition optimized to substantially eliminate formation of chemical and intra- and intergranular precipitates in the bulk material; and removing the deposited generally tubular, unpatterned crystalline metal film from the generally cylindrical substrate.

The methods, systems, and apparatuses are set forth in part in the description which follows, and in part will be obvious from the description, or can be learned by practice of the methods, apparatuses, and systems. The advantages of the methods, apparatuses, and systems will be realized and attained by means of the elements and combinations particularly pointed out in the appended claims. It is to be understood that both the foregoing general description and the following detailed description are exemplary and explanatory only and are not restrictive of the methods, apparatuses, and systems, as claimed.

BRIEF DESCRIPTION OF THE DRAWINGS

In the accompanying figures, like elements are identified by like reference numerals among the several preferred embodiments of the present invention.

FIG. 1 is a perspective view of the inventive endoluminal stent.

FIG. 2A is a fragmentary side elevational view of a first embodiment of the present invention depicting the inventive endoluminal stent in its radially unexpanded configuration.

FIG. 2B is a fragmentary side elevational view of the first embodiment of the present invention in its radially expanded configuration.

FIG. 3A is a fragmentary side elevational view of a second embodiment of the present invention in its radially unexpanded configuration.

FIG. 3B is a fragmentary side elevational view of the first embodiment of the present invention in its radially expanded configuration.

FIG. 4A is a fragmentary side elevational view of a third embodiment of the present invention in its radially unexpanded configuration.

FIG. 4B is a fragmentary side elevational view of the third embodiment of the present invention in its radially expanded configuration.

FIG. 5 is a side elevational view of a portion of a fourth embodiment of the present invention in its radially unexpanded configuration.

FIG. 6A is a photomicrograph of section 6A in FIG. 5.

FIG. 6B is a photomicrograph of section 6B in FIG. 5.

FIG. 7 is a fragmentary side elevational view of a fifth embodiment of the present invention in its radially unexpanded configuration.

FIG. 8 is a fragmentary side elevational view of a sixth embodiment of the present invention in its radially unexpanded configuration.

FIG. 9 is a fragmentary side elevational view of a seventh embodiment of the present invention in its radially unexpanded configuration.

FIG. 10A is a diagrammatic cross-sectional view taken along line 10A-10A of FIG. 7 illustrating a first construction of the present invention.

FIG. 10B is a diagrammatic cross-sectional view taken along line 10B-10B of FIG. 7 illustrating a second construction of the present invention.

FIG. 10C is a diagrammatic cross-sectional view taken along line 10C-10C of FIG. 7 illustrating the Z-axis profile of each of the plurality of first structural elements of the present invention.

FIG. 10D is a diagrammatic cross-sectional view taken along line 10D-10D of FIG. 7 illustrating the Z-axis profile of each of the plurality of second structural elements of the present invention.

FIG. 11A is a fragmentary elevational view of an eighth embodiment of the present invention in its radially unexpanded state.

FIG. 11B is a fragmentary elevational view of the eighth embodiment of the present invention in its radially expanded state.

FIG. 11C is a side elevational view illustrating the eighth embodiment of the inventive endoluminal stent.

FIG. 12 is a perspective view of a self-supporting graft in accordance with the present invention.

FIG. 13 is a cross-sectional view taken along line 13-13 of FIG. 12.

DETAILED DESCRIPTION OF THE INVENTION

The foregoing and other features and advantages of the invention are apparent from the following detailed description of exemplary embodiments, read in conjunction with the accompanying drawings. The detailed description and drawings are merely illustrative of the invention rather than limiting, the scope of the invention being defined by the appended claims and equivalents thereof.

Endoluminal stent and stent-graft design inherently attempts to optimize the functional aspects of radial expandability, i.e., the ratio of delivery diameter to expanded diameter, hoop strength, longitudinal flexibility, column strength, fish-scaling of individual structural members of the stent, fatigue life, corrosion resistance, corrosion fatigue, hemodynamics, biocompatibility and the capability of stent-through-stent delivery. Conventional stent designs have had to compromise one or more functional features of a stent in order to maximize a particular functionality, e.g., longitudinal flexibility is minimized in order to achieve desirable column strength or high hoop strengths are achieved at the expense of small ratios of radial expandability. It is an objective of the present invention to provide designs for endoluminal unibody stents that achieve balances between the ratio of radial expandability, hoop strength, longitudinal flexibility and column strength, with biocompatibility, hemodynamics, radioopacity, minimal or no fish-scaling and increased capacity for endothelialization.

An endoluminal stent and self-supporting endoluminal graft is disclosed each of which is formed from generally two interconnecting structural regions. First structural regions define circumferential sections of the endoluminal stent, provide the endoluminal stent with hoop strength, and are regions of relatively higher stent pattern density. The first structural regions are formed of a plurality of structural elements oriented circumferentially about the stent and are arrayed in adjacent, spaced-apart relationship with one another along the longitudinal axis of the endoluminal stent. Second structural regions define longitudinal support sections that interconnect adjacent circumferential sections in adjacent pairs of first structural regions and provide longitudinal or column strength to the endoluminal stent. The second structural regions are formed of a plurality of structural members oriented generally parallel to the longitudinal axis of the endoluminal stent and generally perpendicular to the orientation of the structural elements forming the first structural regions and are arrayed about the circumference of the endoluminal stent.

Two general embodiments of the stent of the present invention are disclosed. A first embodiment consists of second structural regions comprised of a plurality of longitudinal structural members each of which has a generally sinusoidal configuration along the longitudinal axis of the endoluminal stent, and the first structural regions are comprised of a plurality of sinusoidal structural elements that interconnect adjacent pairs of the structural elements of the second structural regions. This first embodiment is generally referred to herein as the “longitudinally flexible stent”. A second embodiment consists of second structural regions comprised of a plurality of generally linear second structural members which extend the entire longitudinal axis of the endoluminal stent; the first structural regions are comprised of a plurality of sinusoidal structural elements which interconnect adjacent pairs of the plurality of generally linear second structural elements in spaced apart relationship. This second embodiment is generally referred to as the “columnar stent”. For purposes of the present application, an individual structural element with a serpentine pattern or a zig-zag configuration having either regular or irregular periodicity or both in the some or all of the peaks and troughs is referred to as being “sinusoidal” or having a “sine-wave configuration.”

In accordance with a first preferred embodiment of the inventive endoluminal stent, there is provided endoluminal stent that is comprised of a plurality of first structural elements that together form the circumference of the stent and extending along the longitudinal axis of the stent, and a plurality of second structural elements that interconnect adjacent pairs of first structural elements. Each of the plurality of first structural elements has a generally sinusoidal configuration with a regular or irregular periodicity or both between the peaks and troughs of the pattern, with the peaks and troughs projecting from the first structural elements in the circumferential axis. The plurality of second structural elements are generally linear members which interconnect an apex of a peak of one of the plurality of first structural elements with an apex of a valley of a second and adjacent one of the plurality of first structural elements. Each of the plurality of second structural elements are generally oriented parallel to the longitudinal axis of the stent.

The plurality of first structural elements is arrayed about and forms the circumference of the stent, with individual first structural elements extending parallel to the longitudinal axis of the stent. Each of the plurality of first structural elements preferably extends substantially the entire longitudinal axis of the stent, however, it is contemplated that some or all of the plurality of first structural elements may be oriented parallel to the longitudinal axis of the stent without extending substantially the entire longitudinal axis of the stent. Each of the plurality of first structural elements generally has a sine-wave configuration with the element being formed into successive peaks and troughs extending along the longitudinal axis of the stent. Again, it will be understood that the terms “sine-wave configuration” or “sinusoidal” are intended to include elements which have peaks and troughs with regular or irregular periodicity throughout the longitudinal axis of the element or which have peaks and troughs with regions of regular and regions of irregular periodicity along the longitudinal axis of the element, the peaks and troughs and the apices of the peaks and troughs may have many shapes, including, without limitation, regular curves, irregular curves, Z-shaped, U-shaped or the like. The plurality of first structural elements are arrayed in phase with one another, such that the peaks and troughs of one of the plurality of first structural elements in circumferentially aligned with the peaks and troughs of an adjacent first structural elements.

Each of the plurality of second structural elements comprises generally linear members which interconnect adjacent pairs of first structural elements. Each of the plurality of second structural elements is either integral with or conjoined the first structural elements with which it is associated. Each of the plurality of second structural elements joins to a trough of one first structural element with a peak of a second first structural element, with successive troughs of one first structural element being joined with successive peaks of the second first structural element.

Alternatively, in accordance with a second preferred embodiment of the present invention, the inventive endoluminal stent may consist of a plurality of substantially linear first structural elements oriented parallel to the longitudinal axis of the stent and a plurality of generally sinusoidal second structural elements which interconnect adjacent pairs of the first structural elements and extend generally about the circumferential axis of the stent. Each of the plurality of first structural elements preferably extends substantially the entire longitudinal axis of the stent, again, however, it is contemplated that some or all of the plurality of first structural elements may be oriented parallel to the longitudinal axis of the stent without extending substantially the entire longitudinal axis of the stent. The plurality of generally sinusoidal second structural elements form the circumferential links of the stent, and permit radial expansion, either by an applied radially outwardly directed force which plastically deforms the second structural elements, under inherent spring tension or as a result of shape memory properties of the stent material, or combinations thereof.

In accordance with all embodiments of the present invention, the plurality of first structural elements and the plurality of second structural elements may be fabricated of like biocompatible materials, preferably, biocompatible metals or metal alloys. In this manner, both the plurality of first structural elements and the plurality of second structural elements have like physical material properties, e.g., tensile strength, modulus of elasticity, plastic deformability, spring bias, shape memory or super-elastic properties. Alternatively, the plurality of first structural elements and the plurality of second structural elements may be fabricated of biocompatible materials, preferably, biocompatible metals or metal alloys which exhibit different physical or material properties. In this latter case, the plurality of first structural elements may, for example, be fabricated of a plastically deformable material, such as stainless steel, while the plurality of second structural elements are fabricated of a shape memory or super-elastic material, such as nickel-titanium alloys, or of a spring biased material, such as stainless steel.

Heretofore, joints between discrete sections of endoluminal stents required welds in order to join sections of the stent. One particular advantage of the present invention is that by forming the stent using vapor deposition techniques, not only are discrete sections atomically joined without the use of welds, but different materials may be employed in different and discrete sections of the stent in order to impart distinct material properties and, therefore, functionality, to the discrete sections.

Finally, the present invention also includes a self-supporting endoluminal graft. As used herein the term “graft” is intended to indicate any type of tubular member that exhibits integral columnar and circumferential strength and which has openings that pass through the thickness of the tubular member. The inventive self-supporting endoluminal graft preferably consists of a member formed of at least one of a plurality of layers, each layer being comprised of a plurality of first and second structural elements which intersect one another, as described above, to define a plurality of open regions between intersecting pairs of the first and second structural elements. A web region subtends at least a portion of the open region to at least partially enclose each of the plurality of open regions. Successive adjacent layers of the plurality of layers are positioned such that the open regions are staggered in the Z-axis transverse through the wall of the self-supporting endoluminal graft. By staggering the open regions, interlamellar spaces are created to facilitate endothelialization of the endoluminal graft.

The inventive endoluminal stent may be, but is not necessarily, fabricated by vapor deposition techniques. Vapor deposition fabrication of the inventive stents offers many advantages, including, without limitation, the ability to fabricate stents of complex geometries, the ability to control fatigue life, corrosion resistance, corrosion fatigue, bulk and surface material properties, and the ability to vary the transverse profiles, Z-axis thickness and X-Y-axis surface area of the stent's structural elements in manners that affect the longitudinal flexibility, hoop strength of the stent and radial expansion profiles.

In accordance with the present invention there is provided several preferred embodiments. In each of the preferred embodiments of the present invention, the general configuration of the inventive endoluminal stent is identical. With particular reference to FIG. 1, the inventive endoluminal stent 10 consists generally of a tubular cylindrical element having a stent wall 12 that defines a central lumen 14 of the stent. A plurality of first structural elements 16 are arrayed about the circumferential axis C′ of the stent 10 and extend parallel along the longitudinal axis of stent 10. A plurality of second structural elements 18 interconnects adjacent pairs of the plurality of first structural elements 16. Each of the plurality of first structural elements 16 have a generally sinusoidal configuration with a plurality of peaks 16 a and a plurality of troughs 16 b of each first structural element. As noted above, the plurality of peaks 16 a and the plurality of troughs 16 b may have either regular or irregular periodicity along the longitudinal axis of each of the plurality of first structural elements 16 or each of the plurality of first structural elements may have regions of regular periodicity and regions of irregular periodicity. Each of the plurality of second structural elements preferably comprise linear elements which interconnect a peak 16 a of a first one of the first structural elements 16 with a trough 16 b of a second one of the first structural elements adjacent the first one of the first structural elements 16.

The plurality of first 16 and second 18 structural elements are preferably made of materials selected from the group consisting of elemental titanium, vanadium, aluminum, nickel, tantalum, zirconium, chromium, silver, gold, silicon, magnesium, niobium, scandium, platinum, cobalt, palladium, manganese, molybdenum and alloys thereof, and nitinol and stainless steel. The plurality of first structural elements 16 and the plurality of second structural elements 18 may be made of the same material or of different materials and have the same material properties or have different material properties. The term “material properties” is intended to encompass physical properties, including without limitation, elasticity, tensile strength, mechanical properties, hardness, bulk and/or surface grain size, grain composition, and grain boundary size, intra and inter-granular precipitates. Similarly, the materials selected for the plurality of first structural elements 16 and the plurality of second structural elements 18 may be selected to have the same of different chemical properties. The term “chemical properties” is intended to encompass both any chemical reaction and change of state that the material may undergo after being implanted into a body and the physiological response of the body to the material after implantation.

The inventive stent 10, including the plurality of first structural elements 16 and second structural elements 18, is preferably made of a bulk material having controlled heterogeneities on the luminal surface thereof. As is described in co-pending, commonly assigned, U.S. patent application Ser. No. 09/443,929, filed Nov. 19, 1999, which is hereby incorporated by reference, heterogeneities are controlled by fabricating the bulk material of the stent to have defined grain sizes, chemical and intra and intergranular precipitates and where the bulk and surface morphology differ, yielding areas or sites along the surface of the stent while maintaining acceptable or optimal protein binding capability. The characteristically desirable properties of the inventive stent are: (a) optimum mechanical properties consistent with or exceeding regulatory approval criteria, (b) minimization of defects, such as cracking or pin hole defects, (c) a fatigue life of 400 MM cycles as measured by simulated accelerated testing, (d) corrosion and/or corrosion-fatigue resistance, (e) biocompatibility without having biologically significant impurities in the material, (f) a substantially non-frictional abluminal surface to facilitate atraumatic vascular crossing and tracking and compatible with transcatheter techniques for stent introduction, (g) radiopaque at selected sites and MRI compatible, (h) have a luminal surface which is optimized for surface energy and microtopography, (i) minimal manufacturing and material cost consistent with achieving the desired material properties, and (j) high process yields.

In accordance with the present invention, the foregoing properties are achieved by fabricating a stent by the metal deposition methodologies used in the microelectronics and nano-fabrication vacuum coating arts, and which are hereby incorporated by reference. The preferred deposition methodologies include ion-beam assisted evaporative deposition and sputtering techniques. In ion beam-assisted evaporative deposition it is preferable to employ dual and simultaneous thermal electron beam evaporation with simultaneous ion bombardment of the substrate using an inert gas, such as argon, xenon, nitrogen or neon. Bombardment with an inert gas, such as argon ions serves to reduce void content by increasing the atomic packing density in the deposited material during deposition. The reduced void content in the deposited material allows the mechanical properties of that deposited material to be similar to the bulk material properties. Deposition rates up to 20 nm/sec are achievable using ion beam-assisted evaporative deposition techniques.

When sputtering techniques are employed, a 200-micron thick stainless steel film may be deposited within about four hours of deposition time. With the sputtering technique, it is preferable to employ a cylindrical sputtering target, a single circumferential source that concentrically surrounds the substrate that is held in a coaxial position within the source.

Alternate deposition processes which may be employed to form the stent in accordance with the present invention are cathodic arc, laser ablation, and direct ion beam deposition. When employing vacuum deposition methodologies, the crystalline structure of the deposited film affects the mechanical properties of the deposited film. These mechanical properties of the deposited film may be modified by post-process treatment, such as by, for example, annealing, high-pressure treatment or gas quenching.

Materials to make the inventive stents are chosen for their biocompatibility, mechanical properties, i.e., tensile strength, yield strength, and their ease of deposition include the following: elemental titanium, vanadium, aluminum, nickel, tantalum, zirconium, chromium, silver, gold, silicon, magnesium, niobium, scandium, platinum, cobalt, palladium, manganese, molybdenum and alloys thereof, such as zirconium-titanium-tantalum alloys, nitinol, and stainless steel.

During deposition, the chamber pressure, the deposition pressure and the partial pressure of the process gases are controlled to optimize deposition of the desired species onto the substrate. As is known in the microelectronic fabrication, nano-fabrication and vacuum coating arts, both the reactive and non-reactive gases are controlled and the inert or non-reactive gaseous species introduced into the deposition chamber are typically argon and nitrogen. The substrate may be either stationary or moveable, either rotated about its longitudinal axis, or moved in an X-Y plane within the reactor to facilitate deposition or patterning of the deposited material onto the substrate. The deposited material maybe deposited either as a uniform solid film onto the substrate, or patterned by (a) imparting either a positive or negative pattern onto the substrate, such as by etching or photolithography techniques applied to the substrate surface to create a positive or negative image of the desired pattern or (b) using a mask or set of masks which are either stationary or moveable relative to the substrate to define the pattern applied to the substrate. Patterning may be employed to achieve complex finished geometries of the resultant stent, both in the context of spatial orientation of the pattern as well as the material thickness at different regions of the deposited film, such as by varying the wall thickness of the material over its length to thicken sections at proximal and distal ends of the stent to prevent flaring of the stent ends upon radial expansion of the stent.

The stent may be removed from the substrate after stent formation by any of a variety of methods. For example, the substrate may be removed by chemical means, such as etching or dissolution, by ablation, by machining or by ultrasonic energy. Alternatively, a sacrificial layer of a material, such as carbon or aluminum, may be deposited intermediate the substrate and the stent and the sacrificial layer removed by melting, chemical means, ablation, machining or other suitable means to free the stent from the substrate.

The resulting stent may then be subjected to post-deposition processing to modify the crystalline structure, such as by annealing, or to modify the surface topography, such as by etching to affect and control the heterogeneities on the blood flow surface of the stent.

A plurality of microgrooves may be imparted onto the luminal and/or abluminal surface of the stent 10, as is more fully described in International Publication No. WO 99/23977, published 20 May 1999, which is commonly assigned with the present application and is hereby incorporated by reference. The plurality of microgrooves may be formed either as a post-deposition process step, such as by etching, or during deposition, such as by depositing the stent-forming material onto a mandrel which has a microtopography on the surface thereof which causes the metal to deposit with the microgroove pattern as part of the deposited material.

Each of the preferred embodiments of the present invention are preferably fabricated by employing a vapor deposition technique which entails vapor depositing a stent-forming metal onto a substrate. The substrate may be planar or cylindrical and is either pre-patterned with one of the preferred geometries of first and second structural elements, in either positive or negative image, or the substrate may be un-patterned. Where the substrate is un-patterned, the deposited stent-forming metal is subjected to post-deposition patterning to pattern the deposited stent-forming metal into one of the preferred geometries of the first and second structural elements. In all embodiments of the present invention fabricated by vapor deposition techniques, the need for post-deposition processing of the patterned endoluminal stent, e.g., modifying the surface of the stent by mechanical, electrical, thermal or chemical machining or polishing, is eliminated or minimized.

Vapor deposition fabrication of the inventive endoluminal stents offers many advantages, including, for example, the ability to fabricate stents of complex geometries, ultrafine dimensional tolerances on the order of Angstroms, the ability to control fatigue life, corrosion resistance, corrosion fatigue, inter- and intra-granular precipitates and their effect on corrosion resistance and corrosion fatigue, bulk material composition, bulk and surface material properties, radioopacity, and the ability to vary the transverse profiles, Z-axis thickness and X-Y-axis surface area of the stent structural elements in manners that affect the longitudinal flexibility, hoop strength, and radial expansion behavior and profile of the stent. Bulk material composition may be adjusted to employ elemental fractions in alloy compositions that are not feasible when using conventionally formed metals. This results in achieving the ability to tailor the alloy compositions in a manner that optimizes the alloy composition for a desired material or mechanical property. For example, nickel-titanium tubes exhibiting shape memory and/or superelastic properties were made employing in excess of 51.5 atomic percent nickel, which is not achievable using conventional working techniques due to high plateau stresses exhibited by the material. Specifically, the present inventors have fabricated nickel-titanium alloy tubes employing the method of the present invention that contain between 51.5 and 55 atomic percent nickel.

Vapor deposition of the inventive endoluminal stent, in accordance with a preferred embodiment of the present invention, significantly reduces or virtually eliminates inter- and intra-granular precipitates in the bulk material. It is common practice in the nickel-titanium endoluminal device industry to control transition temperatures and resulting mechanical properties by altering local granular nickel-titanium ratios by precipitation regimens. In the present invention, the need to control precipitates for mechanical properties is eliminated. Where nickel-titanium is employed as the stent-forming metal in the present invention, local nickel-titanium ratios will be the same or virtually identical to the nickel-titanium ratios in the bulk material, while still allowing for optimal morphology and eliminating the need for employing precipitation heat treatment. The resulting deposited stent-forming metal exhibits superior corrosion resistance, and hence, resistance to corrosion fatigue, when compared to conventional wrought nickel-titanium alloys.

The plurality of first structural elements 16 and the plurality of second structural elements 18 are preferably conformationally configured curing vapor deposition to impart a generally ovular or elliptical transverse cross-sectional profile and have chamfered or curved leading and trailing luminal and abluminal surface edges in the longitudinal axis of the stent in order to provide better blood flow surface profiles.

Turning to FIGS. 2-4, there are illustrated three preferred embodiments of the present invention. Each embodiment is depicted in its diametrically unexpanded state in the A Figure and in its diametrically expanded state in the B Figure. Thus, FIG. 2A represents a first embodiment of the inventive endoluminal stent in its diametrically unexpanded state, while FIG. 2B represents the first embodiment of the inventive endoluminal stent in its diametrically expanded state.

With specific reference to FIGS. 2A and 2B, there is illustrated stent 20 that consists of a plurality of first structural elements 22 and a plurality of second structural elements 24 which interconnect adjacent pairs of the plurality of first structural elements 22. Each of the plurality of first structural elements 22 extends parallel to the longitudinal axis L′ of the stent 20, while each of the plurality of second structural elements 24 are arrayed in the circumferential axis C′ of the stent 20. Each of the first structural elements 22 has a sinusoidal configuration consisting of a plurality of successive peaks 26 and troughs 28. The plurality of first structural elements 22 are arrayed about the circumference of stent 20 such that the peaks 26 and the troughs 28 of each individual first structural element 22 are in phase with respect to adjacent peaks 26 and troughs 28 of adjacent first structural elements 22.

The plurality of second structural elements 24 interconnect adjacent pairs of first structural elements 22. Each second structural element 24 has a first end 24 a that connects with a trough 28 of a first structural element 22 and a second end 24 b that connects with a peak 26 of an adjacent structural element 22. The plurality of second structural elements 24 serve to maintain the plurality of first structural elements in spaced-apart relationship relative to one another about the circumference of the stent 20. In accordance with a preferred embodiment of the invention, the first end 24 a of a second structural element 24 couples to a trough 28 such that it is generally tangential to a downward slope 28 s of the trough. Similarly, the second end 24 b of the second structural element 22 couples to a peak 26 of a first structural element 22 such that the second structural element 24 is generally tangential to a downward slope 26 s of the peak 26.

In the unexpanded state depicted in FIG. 2A, each of the plurality of second structural elements 24 have a generally S-shape or sinusoidal shape, however, when the stent is in its diametrically expanded state depicted in FIG. 2B, each of the plurality of second structural elements 24 assumes a generally linear configuration which serves to maintain an enlarged spacing between adjacent pairs of first structural elements 22 than when the stent 20 is in its unexpanded state.

Turning to FIGS. 3A and 3B, there is illustrated a second preferred embodiment of the stent 30 present invention. Like stent 20 described above, stent 30 consists generally of a plurality of first structural elements 32 and a plurality of second structural elements 34 which interconnect adjacent pairs of the plurality of first structural elements 32. Each of the plurality of first structural elements 32 extends parallel to the longitudinal axis L′ of the stent 30, while each of the plurality of second structural elements 34 are arrayed in the circumferential axis C′ of the stent 30. Each of the first structural elements 32 has a generally sinusoidal zigzag or Z-configuration consisting of a plurality of successive peaks 36 and troughs 38. The plurality of first structural elements 32 are arrayed about the circumference of stent 30 such that the peaks 36 and the troughs 38 of each individual first structural element 32 are in phase with respect to adjacent peaks 36 and troughs 38 of adjacent first structural elements 32.

The plurality of second structural elements 34 interconnect adjacent pairs of first structural elements 32. Each second structural element 24 has a first end 34 a, which connects with a trough 38 of a first structural element 32, and a second end 34 b, which connects with a peak 36 of an adjacent structural element 32. The plurality of second structural elements 34 serve to maintain the plurality of first structural elements in spaced-apart relationship relative to one another about the circumference of the stent 30.

In the unexpanded state depicted in FIG. 3A, each of the plurality of second structural elements 34 have a generally linear configuration which is positioned substantially parallel to the longitudinal axis L′ of the stent 30. However, when the stent 30 is in its diametrically expanded state depicted in FIG. 3B, each of the plurality of second structural elements 34 repositions to assume a generally circumferential orientation relative to the stent which, in turn, serves to maintain an enlarged spacing between adjacent pairs of first structural elements 32 than when the stent 30 is in its unexpanded state.

Turning to FIGS. 4A and 4B, there is illustrated a third preferred embodiment of the stent 40 present invention. Like stents 20 and 30 described above, stent 40 consists generally of a plurality of first structural elements 42 and a plurality of second structural elements 44 which interconnect adjacent pairs of the plurality of first structural elements 42. Each of the plurality of first structural elements 42 extends parallel to the longitudinal axis L′ of the stent 40, while each of the plurality of second structural elements 44 are arrayed in the circumferential axis C′ of the stent 40. Each of the first structural elements 42 has a generally sinusoidal zig-zag or Z-configuration consisting of a plurality of successive peaks 46 and troughs 48. Arcuate sections 45 are provided at apices of each of the peaks 46 and the troughs 48. The arcuate sections 45 act as springs for each first structural element 42 to impart axial flexibility and longitudinal compressibility and expandability to the stent 40. The plurality of first structural elements 42 are arrayed about the circumference of stent 40 such that the peaks 46 and the troughs 48 of each individual first structural element 42 are in phase with respect to adjacent peaks 46 and troughs 48 of adjacent first structural elements 42.

The plurality of second structural elements 44 interconnect adjacent pairs of first structural elements 32. Each second structural element 44 has a first end 44 a, which connects with an arcuate section 45 of a trough 48 of a first structural element 42, and a second end 44 b, which connects with an arcuate section 45 of a peak 46 of an adjacent structural element 42. The plurality of second structural elements 44 serve to maintain the plurality of first structural elements in spaced-apart relationship relative to one another about the circumference of the stent 40.

In the unexpanded state depicted in FIG. 4A, each of the plurality of second structural elements 44 have a generally linear configuration and are oriented substantially parallel to adjacent sections of the first structural elements 42 to which it is attached. However, when the stent 40 is in its diametrically expanded state depicted in FIG. 4B, each of the plurality of second structural elements 44 repositions to assume an orientation which is generally parallel to the longitudinal axis L′ of the stent 40 and maintain an enlarged spacing between adjacent pairs of first structural elements 42 than when the stent 40 is in its unexpanded state.

FIGS. 5, 6A and 6B depict another preferred embodiment and the best mode contemplated for the present invention. Like stents 20, 30 and 40 described above, stent 50 consists generally of a plurality of first structural elements 52 and a plurality of second structural elements 54 which interconnect adjacent pairs of the plurality of first structural elements 52. Each of the plurality of first structural elements 52 extends parallel to the longitudinal axis L′ of the stent 50, while each of the plurality of second structural elements 54 are arrayed in the circumferential axis C′ of the stent 50. Each of the first structural elements 52 has a generally sinusoidal zig-zag or Z-configuration consisting of a plurality of successive peaks 56 and troughs 58. The plurality of first structural elements 52 are arrayed about the circumference of stent 50 such that the peaks 56 and the troughs 58 of each individual first structural element 52 are in phase with respect to adjacent peaks 56 and troughs 58 of adjacent first structural elements 52.

The plurality of second structural elements 54 interconnect adjacent pairs of first structural elements 52. Each second structural element 54 has a first end 54 a, which connects with a trough 58 of a first structural element 52, and a second end 54 b that connects with a peak 56 of an adjacent structural element 52. The plurality of second structural elements 54 serve to maintain the plurality of first structural elements in spaced-apart relationship relative to one another about the circumference of the stent 50.

In the unexpanded state depicted in FIG. 5, each of the plurality of second structural elements 54 have a generally linear configuration which is positioned substantially parallel to the longitudinal axis L′ of the stent 50. For purposes of explanation and illustration only, the stent 50 is also referenced with proximal P and distal D orientations relative to the longitudinal axis L′ of the stent 50.

When the stent 50 is in its diametrically expanded state, each of the plurality of second structural elements 54 repositions to assume a generally circumferential orientation relative to the stent which, in turn, serves to maintain an enlarged spacing between adjacent pairs of first structural elements 52 than when the stent 50 is in its unexpanded state.

Each of the plurality of first structural elements 52 further comprise alternating relatively narrower sections 52 a and relatively wider sections 52 b which form each peak 56 and each trough 58 of each first structural element 52. In accordance with the best mode presently contemplated for the present invention, and without limiting the scope of the invention, the preferred ratio of surface area between the wider sections 52 b and the narrower sections 52 a is about 2:1. Thus, for example, if the width W₂ of the narrower section 52 a is about 60 i, the width W₁ of the wider section 52 b will be about 1201. The apices of each peak 56 and each trough 58 are formed by a chamfer or taper between the narrower section 52 a and the wider section 52 b of each peak 56 and each trough 58 of each of the plurality of first structural elements 52. The apex of a typical peak 56 and trough 58 and the chamfered or tapered section, described above, is depicted in the scanning electron photomicrograph at FIG. 6B

Each of the plurality of second structural elements 54 has a generally elongate configuration that connects at a first end 54 a to a trough 58 and at a second end 54 b to a peak 56. Each of the first end 54 a and the second end 54 b connect to adjacent first structural elements 52 and are formed by chamfered sections which project generally at right angles relative to a central longitudinal axis 57 of each of the plurality of second structural elements 54 and connect to a terminal section of the narrower section 52 a of either each peak 56 or each trough 58 of each of the plurality of the first structural elements 52. FIG. 6A depicts with greater particularity a first end 54 a and the chamfered section integrally connecting a second structural element 54 with a first structural element 52. The chamfered sections at first end 54 a and 54 b project in opposing directions relative to one another. Thus, in one embodiment the chamfered section at the first end 54 a projects generally distally relative to the longitudinal axis L′ of stent 50, while the chamfered section at the second end 54 b projects generally proximally relative to the longitudinal axis L′ of stent 50. Those of ordinary skill in the art will understand that the relative directional orientation of the first end 54 a and the second end 54 b may be switched so that the first end 54 a projects generally proximally while the second end 54 b projects generally distally relative to the longitudinal axis L′ of stent 50. Similarly, those of ordinary skill in the art will appreciate that alternate configurations for the first end 54 a and the second end 54 b are contemplated by the present invention. For example, instead of a generally perpendicular orientation between the chamfered section and the longitudinal axis 57 of the second structural element 54, the first end 54 a and the second end 54 b could have alternate angular orientations relative to the first structural element 52 and the second structural element 54.

Turning to FIGS. 7-10, there are illustrated alternate preferred embodiments of the present invention in which a plurality of first structural elements are generally linear members which extend parallel to a longitudinal axis L′ of the stent and a plurality of second structural elements which have a generally sinusoidal shape form the circumferential axis C′ of the stent and permit radial expansion thereof. These alternate preferred embodiments exhibit excellent column strength due to the linear members of the plurality of first structural elements while the configuration of the plurality of second structural elements facilitate low device delivery profiles while allowing for large ratios of radial expansion over the stent's unexpanded diameter.

With particular reference to FIG. 7, there is illustrated a stent 60 which includes a plurality of generally linear first structural elements 62 which extend parallel to and substantially the entire the longitudinal axis L′ of the stent 60. The circumferential axis C′ of the stent 60 is comprises of a plurality of second structural elements 64, each of which has a generally U-shaped configuration. Individual second structural elements 64 interconnect adjacent pairs of first structural elements 62 and maintain the first structural elements 62 in spaced apart relationship from one another. Each individual second structural element 64 is composed of an apex 66, which forms the peak of each second structural element 64, a first connection section 63 and a second connection section 65. The first connection section 63 connects the second structural element 64 to a single first structural element 62, while the second connection section 65 connects the second structural element 64 to an adjacent first structural element 62, thereby maintaining the first structural elements 62 in spaced apart relationship relative to one another. Each of the plurality of second structural elements 64 are either integral with or connected to each of the plurality of first structural elements 62 at intersection points 67 along the circumferential axis C′ of the stent 60. A plurality of second structural elements 64 are aligned in end-to-end fashion, with the first connection section 63 of one second structural element 64 being adjacent to a second connection section 65 of another second structural element, thereby forming a continuous sinusoidal circumferential element 69 which extends about the entire circumferential axis C′ of the stent 60. In the continuous sinusoidal circumferential element 69, peaks of each sinusoidal period are formed by the apices 66 of each generally U-shaped first structural element 64, while troughs 65 of each sinusoidal period are formed by the first connection section 63 of one second structural element 64, the second connection section 65 of another second structural element 64, and their connection point 67 on the first structural element 62.

A plurality of continuous sinusoidal circumferential elements 69 are arrayed in spaced apart relationship along the longitudinal axis L′ of the stent 60 and form the walls of the stent 60. During radial expansion of the stent 60, each of the plurality of second structural elements 64 extends circumferentially along circumferential axis C′ such that the periodicity between successive peaks of each generally U-shaped second structural element 64 increases.

In accordance with this preferred embodiment of stent 60, the apices 66 of each first structural member 64, which forms the peak of each sinusoidal period, have a common directional orientation parallel to and directed either proximally or distally relative to the longitudinal axis L′ of the stent 60. In accordance with a variation of the preferred embodiment of the stent 60, the apices 66 of each first structural member 64 in a first continuous sinusoidal circumferential element 69 are directionally oriented opposite that of the apices 66 of each first structural member in a second, adjacent, continuous sinusoidal circumferential element 69. In this variation, adjacent continuous sinusoidal circumferential elements 69 would be out-of-phase relative to one another, i.e., such as with a sine and cosine functions, with the apices 66 of each sinusoidal element being adjacent one another and one apex 66 oriented proximally and a longitudinally adjacent apex 66 being oriented distally relative to the longitudinal axis L′ of the stent 60.

With particular reference to FIG. 8, there is illustrated an alternate embodiment of the present invention in which stent 70 is again comprised of a plurality of plurality of generally linear first structural elements 72 which extend parallel to and substantially the entire the longitudinal axis L′ of the stent 70. The circumferential axis C′ of the stent 70 is comprises of a plurality of second structural elements 74, each of which has a generally U-shaped configuration.

Individual second structural elements 74 interconnect adjacent pairs of first structural elements 72 and maintain the first structural elements 72 in spaced apart relationship from one another. Each individual second structural element 74 is composed of an apex 76, which forms the peak of each second structural element 74, a first connection section 73 and a second connection section 75. As distinguished from stent 60, in which the apices 66 have a regular curve, each of the apices 76 of stent 70 are formed by generally linear sections which are oriented parallel to the circumferential axis C′ of stent 70.

The first connection section 73 connects the second structural element 74 to a single first structural element 72, while the second connection section 75 connects the second structural element 74 to an adjacent first structural element 72, thereby maintaining the first structural elements 72 in spaced apart relationship relative to one another. Each of the plurality of second structural elements 74 are either integral with or connected to each of the plurality of first structural elements 72 at intersection points 77 along the circumferential axis C′ of the stent 70.

A plurality of second structural elements 74 are aligned in end-to-end fashion, with the first connection section 73 of one second structural element 74 being adjacent to a second connection section 75 of another second structural element, thereby forming a continuous sinusoidal circumferential element 79 which extends about the entire circumferential axis C′ of the stent 70. In the continuous sinusoidal circumferential element 79, peaks of each sinusoidal period are formed by the apices 76 of each generally U-shaped first structural element 74, while troughs 75 of each sinusoidal period are formed by the first connection section 73 of one second structural element 74, the second connection section 75 of another second structural element 74, and their connection point 77 on the first structural element 72.

A plurality of continuous sinusoidal circumferential elements 79 are arrayed in spaced apart relationship along the longitudinal axis L′ of the stent 70 and form the walls of the stent 70. During radial expansion of the stent 70, each of the plurality of second structural elements 74 extends circumferentially along circumferential axis C′ such that the periodicity between successive peaks of each generally U-shaped second structural element 74 increases.

In accordance with this preferred embodiment of stent 70, the continuous sinusoidal circumferential elements 79 are categorized into a plurality of proximal sinusoidal circumferential elements 79 _(p) and a plurality of distal sinusoidal circumferential elements 79 _(d). The sole difference between the proximal 79 _(p) and the distal 79 _(d) sinusoidal circumferential elements is the directional orientation of the apices 76 of each second structural member 74 relative to the longitudinal axis L′ of the stent 70. That is, in the plurality of proximal circumferential elements 79 _(p), the apex 76 is oriented toward the proximal end of the stent 70, while in the plurality of distal circumferential elements 79 _(d), the apex 76 is oriented toward the distal end of the stent 70. Either at a medial line M′ of the stent 70 or at spaced apart longitudinal sections of the stent 70, a proximal sinusoidal circumferential element 79 _(p) is longitudinally adjacent a distal sinusoidal circumferential element 79 _(d) such that apices 76 of each of the proximal sinusoidal circumferential element 79 _(p) are proximate the apices 76 of the adjacent distal sinusoidal circumferential element 79 _(d), i.e., as in a sine and cosine function. In this configuration, stent 70 will have added longitudinal flexibility either at the medial line M′ or at the spaced apart longitudinal sections of the stent 70 where the plurality of proximal sinusoidal circumferential elements 79 _(p) and a plurality of distal sinusoidal circumferential elements 79 _(d) are out of phase relative to one another.

Turning now to FIG. 9, there is illustrated a stent 80 which includes a plurality of generally linear first structural elements 82 which extend parallel to and substantially the entire the longitudinal axis L′ of the stent 80. The circumferential axis C′ of the stent 80 is comprises of a plurality of second structural elements 84, each of which has a generally S-shaped or sine-wave configuration. Individual second structural elements 84 interconnect adjacent pairs of first structural elements 82 and maintain the first structural elements 82 in spaced apart relationship from one another. Each individual second structural element 84 is composed of at least two apices 66, 68, which project in opposing directions relative to the longitudinal axis L′ of the stent 80, a first connection section 83 and a second connection section 85. The first connection section 83 connects the second structural element 84 to a single first structural element 82, while the second connection section 85 connects the second structural element 84 to an adjacent first structural element 82, thereby maintaining the first structural elements 82 in spaced apart relationship relative to one another. Each of the plurality of second structural elements 84 are either integral with or connected to each of the plurality of first structural elements 82 at intersection points 87 along the circumferential axis C′ of the stent 80. A plurality of second structural elements 84 are aligned in end-to-end fashion, with the first connection section 83 of one second structural element 84 being adjacent to a second connection section 85 of another second structural element, thereby forming a continuous circumferential element 89 which extends about the entire circumferential axis C′ of the stent 80. A plurality of continuous circumferential elements 89 are arrayed in spaced apart relationship along the longitudinal axis L′ of the stent 80 and form the walls of the stent 80.

In accordance with this preferred embodiment of stent 80, the apices 86 of each second structural element 84 have a common directional orientation parallel to and directed either proximally or distally relative to the longitudinal axis L′ of the stent 80. Similarly, the apices 88 of each second structural element 84 have a common directional orientation parallel to and directed either proximally or distally relative to the longitudinal axis L′ of the stent 80. Thus, all apices 86 and all apices 88 are in phase relative to like apices on longitudinally adjacent second structural elements 84. In accordance with a variation of the preferred embodiment of the stent 80, the apices 86 of each second structural element 84 in a first continuous circumferential element 69 are directionally oriented opposite that of the apices 86 of each second structural element 84 in a second, adjacent, continuous circumferential element 89. In this variation, adjacent continuous circumferential elements 89 would be out-of-phase relative to one another, i.e., such as with a sine and cosine functions, with the apices 86 of each second structural element 84 being longitudinally adjacent one another and one apex 86 oriented proximally and a longitudinally adjacent apex 86 being oriented distally relative to the longitudinal axis L′ of the stent 80.

FIGS. 10A and 10B illustrate alternate constructions of the inventive stent. For purposes of the following discussion, it will be noted that the particular stent geometry is a matter of choice and includes, but is not limited to the inventive stents 10, 20, 30, 40, 50, 60 70 and 80 described above. As noted above, the stent of the present invention may be fabricated of materials selected from the group consisting of elemental titanium, vanadium, aluminum, nickel, tantalum, zirconium, chromium, silver, gold, silicon, magnesium, niobium, scandium, platinum, cobalt, palladium, manganese, molybdenum, and alloys thereof, nitinol and stainless steel.

Because the method of making the inventive stent involves utilizing vacuum deposition technologies well known in the microelectronics arts, either a single material may be employed or plural materials may be employed to make either or both the plurality of first structural elements 62 and the plurality of second structural elements 64 or portions thereof. Where plural materials are employed in the vacuum deposition fabrication of a stent, such as, for example, inventive stents 10, 20, 30, 40, 50, 60, 70 or 80, intersection points 65, for example, between first structural elements 62 and the first connection end 63 of one second structural element 64 and a second connection end 68 of another second structural element 64 may be either as a monolayer of alloyed metals used to form the first structural element 62 and the second structural element 64 as illustrated in FIG. 10A or as a multiplayer of non-alloyed metals as illustrated in FIG. 10B. The monolayer depicted in FIG. 10A is comprised of the metal used to form the first structural element 62 that has been deposited first, alloyed with the metal used to form the second structural element 64, which was deposited as a second step. The multi-layer depicted in FIG. 10B is comprised of a layer of metal forming the first structural element 62 which is deposited as a first step, then depositing a layer of metal used to form the second structural element 64 using non-alloying materials.

FIGS. 10C and 10D illustrate transverse cross-sectional views through a second structural member 64 and a first structural member 62, respectively for all embodiments of the inventive endoluminal stent. Conventional stents typically have structural elements with generally quadrilateral transverse shapes. Typically, this is a result of using a hypotube as the starting material for stent formation. The endoluminal stents in accordance with the present invention present first and second structural elements 62, 64 which have radiused lateral surfaces 62 a, 64 a, respectively. In addition, each of the first and second structural elements 62, 64 also have leading and trailing surfaces which are also radiused (not shown). In this manner, all blood contact surfaces of the inventive endoluminal stent present a curvilinear surface to the blood flow thereby facilitating a more laminar blood flow over the structural elements of the inventive endoluminal stent.

An alternative embodiment of the longitudinally flexible stent of the present invention is illustrated in FIGS. 11A-11C. Like the embodiments described above, longitudinally flexible stent 100 is comprised of a plurality of first structural elements 102 and a plurality of second structural elements 104. The first structural elements 102 are positioned generally parallel to the longitudinal axis L′ of the endoluminal stent 100 and are arrayed circumferentially about the circumferential axis C′ of the endoluminal stents 100. The plurality of second structural elements 104 are oriented generally parallel to the circumferential axis C′ of the endoluminal stent 100 and interconnect adjacent pairs of the first structural elements 102 in spaced apart relationship about the circumferential axis C′ of the endoluminal stent 100. Each of the plurality of second structural elements 104 preferably has a sinusoidal configuration with at least one complete sine curve, i.e., having both positive and negative amplitude in the proximal and distal directions relative to the longitudinal axis L′ of the endoluminal stent 100, being subtended between adjacent pairs of the first structural elements 102. A plurality of flex regions 110 is formed in each of the plurality of first structural members 102. Each of the plurality of flex regions 110 are formed as narrowed regions of the first structural member 102 and may be configured as V-shaped projections which project circumferentially from each of the plurality of first structural members 102. In accordance with the best mode for the present invention, it is contemplated that one of the plurality of flex regions 110 is positioned intermediate adjacent pairs of the second structural elements 104 along the first structural element 102. Alternative configurations are additionally contemplated in which the flex regions 110 are positioned between alternative pairs of second structural elements 104, are positioned only at proximal, distal or intermediate regions of the endoluminal stent, or are positioned only on selected first structural elements 102, or combinations thereof. In this manner, the longitudinal flexibility of the endoluminal stent 100 may be tailored to impart greater coefficients of longitudinal flexibility in different regions of the endoluminal stent 100.

In each of the foregoing embodiments, the, Z-axis thickness and X-Y-axis surface area of the stent first and second structural elements may be varied so as to affect the longitudinal flexibility, hoop strength and radial expansion behavior and profile of the stent. For example, a longitudinally intermediate circumferential region of the endoluminal stent may have both first and/or second structural elements which have a greater Z-axis wall thickness than proximal and distal circumferential regions of the stent. This configuration effectively reinforces the intermediate circumferential region, with the result being that the proximal and distal circumferential regions of the stent will radially dilate before the intermediate circumferential region. Alternatively, either or both of the proximal and distal circumferential regions may have first and/or second structural elements which have greater Z-axis wall thicknesses than those in a longitudinally intermediate circumferential region. This configuration will result in the longitudinally intermediate circumferential region radially dilating prior to either or both of the proximal and distal circumferential regions. Another alternative is to vary the Z-axis wall thickness of the first and/or second structural elements in a continuum along the longitudinal axis of the endoluminal stent such that the stent radially expands into a conical configuration.

Finally, in accordance with the present invention there is provided a self-supporting endoluminal graft 90 as depicted in FIG. 12. In accordance with a preferred embodiment of the invention, a graft member is formed as a discrete thin sheet or tube of biocompatible metals or metal-like material or as a laminated or plied structure of a plurality of thin sheets or tubes in adjoining relationship with one another. Like the inventive endoluminal stent, described above, the thin sheet or tube includes a plurality of first structural elements 94 that provide longitudinal or column strength to the graft, and a plurality of second structural elements 96 that provide circumferential or hoop strength to the graft. The first and second structural elements 94, 96 form integral and monolithic elements of the graft. A web 95 of the material that forms the first and second structural elements partially subtends interstitial openings 92 defined between proximate first and second structural elements 94, 96. It is preferable that the thin sheet or tube be comprised of pluralities of openings 98, which pass transversely through the web 95 of the graft member 90. The plurality of openings 98 may be random or may be patterned. It is preferable that the size of each of the plurality of openings be such as to permit cellular migration through each opening, without permitting fluid flow there through. In this manner, blood cannot flow through the plurality of openings, but various cells or proteins may freely pass through the plurality of openings to promote graft healing in vivo. The inventive self-supported endoluminal graft 90 may be fabricated of two or more discrete members each consisting of the inventive endoluminal stent described above which are concentrically engaged relative to one another, and positioned such that interstitial openings 92 in each stent member are juxtaposed adjacent a first or second structural element 94, 96 of an adjacent stent. In this manner the interstitial openings 92 of each stent 90 are at least partially occluded by the first and/or second structural elements 94, 96 of an adjacent endoluminal stent 90. Alternatively, the inventive self-supported endoluminal graft 90 may be fabricated by vacuum deposition techniques as described in co-pending, commonly assigned, U.S. patent application Ser. No. 09/443,929, filed Nov. 19, 1999, which is hereby incorporated by reference. Where the self-supported endoluminal graft is fabricated by vacuum deposition techniques, the graft may be fabricated as a laminated or plied structure in which the first and second structural elements 94, 96 of a first layer are integral and monolithic with one another, as is the web 95 which subtends the interstitial space 92 between adjacent first and second structural elements 94, 96.

With particular reference to FIG. 13 there is illustrated a laminated self-supported graft 90 in accordance with the present invention. Graft 90 is comprised of plural stent layers 90 a, 90 b, 90 c, 90 d which are successively deposited onto one another starting with first stent layer 90 a. First stent layer 90 a is comprised of a plurality of first structural elements 94 and second structural elements 96, with a plurality of web regions 95, each of which subtend a space 99 defined by the first and second structural elements. At least one opening 98 is provided in at least a portion of the web regions 95. A second stent layer 90 b is deposited onto the first stent layer 90 a. Like the first stent layer 90 a, second stent layer 90 b is comprised of a plurality of first structural elements 94 and second structural elements 96, with a plurality of web regions 95, each of which subtend a space 99 defined by the first and second structural elements. Second stent layer 90 b may be of similar geometry or different geometry than first stent layer 90 a, and is positioned out-of-phase relative to the geometric pattern of first stent 90 a. In being out-of-phase with first stent layer 90 a, the first structural element 94 of the second stent layer 90 b is adjacent and overlays both the second structural elements 96, the plurality of web regions 95 and the openings 98 in the first stent layer 90 a. Successive stent layers 90 c, 90 d, and so forth depending upon the particular desired graft construction, are deposited upon one another such that adjacent stent layers form interlamellar endothelial growth channels 97 between successive stent layers 90 a, 90 b, 90 c and 90 d. The interlamellar endothelial growth channels 97 promote endothelialization by providing tortuous micropathways for cellular incorporation into the self-supporting graft 90.

While the present inventions have been described with reference to their preferred embodiments, those of ordinary skill in the art will understand and appreciate that a multitude of variations on the foregoing embodiments are possible and within the skill of one of ordinary skill in the vapor deposition and stent fabrication arts, and that the above-described embodiments are illustrative only and are not limiting the scope of the present invention which is limited only by the claims appended hereto. 

What is claimed is:
 1. A method of manufacturing a device, comprising: a. vacuum depositing a device-forming metal onto an unpatterned, exterior surface of a generally cylindrical substrate to form a generally tubular, unpatterned crystalline metal film under at least one vacuum deposition process condition selected from at least one of chamber pressure, deposition pressure, and partial pressure of a process gas, said at least one process condition optimized to substantially eliminate formation of chemical and intra- and intergranular precipitates in the bulk material; and b. removing the deposited generally tubular, unpatterned crystalline metal film from the generally cylindrical substrate.
 2. The method according to claim 1, further comprising a step of depositing a sacrificial material layer onto the substrate prior to step (a) and removing the sacrificial material layer in order to remove the deposited generally tubular, unpatterned crystalline metal film from the substrate in step (b), and wherein the process condition controlled is a deposition rate and the deposition rate is no less than about 20 nm/sec.
 3. The method according to claim 1, wherein step (a) is conducted by ion beam-assisted evaporative deposition.
 4. The method according to claim 1, wherein step (a) is conducted by sputtering.
 5. The method according to claim 3, wherein the ion beam-assisted evaporative deposition is conducted in the presence of an inert gas.
 6. A method of manufacturing a metal, comprising: a. vacuum depositing a metal onto an unpatterned, exterior surface of a generally cylindrical substrate to form a generally tubular, unpatterned crystalline metal film under at least one vacuum deposition process condition selected from at least one of chamber pressure, deposition pressure, and partial pressure of a process gas, said at least one process condition optimized to minimize formation of chemical and intra- and intergranular precipitates in the bulk material; b. defining the plurality of first and second structural elements in the unpatterned metal film; and c. removing the first and second structural elements from the generally cylindrical substrate.
 7. The method according to claim 6, further comprising a step of depositing a sacrificial material layer onto the substrate prior to step (a) and removing the sacrificial material layer in order to remove the first and second structural elements from the substrate in step (c).
 8. The method according to claim 6, wherein step (a) is conducted by ion beam-assisted evaporative deposition.
 9. The method according to claim 6, wherein step (a) is conducted by sputtering.
 10. The method according to claim 8, wherein the ion beam-assisted evaporative deposition is conducted in the presence of an inert gas.
 11. The method according to claim 10, wherein the inert gas is selected from the group consisting of argon, xenon, nitrogen and neon.
 12. The method according to claim 6, wherein the process condition controlled is a deposition rate and the deposition rate is no less than about 20 nm/sec.
 13. The method according to claim 6, wherein during the deposition of the metal, the substrate is rotated.
 14. A method of manufacturing a device, comprising: a. vacuum depositing nickel and titanium onto an exterior surface of a generally cylindrical substrate to form a deposited generally tubular, crystalline nickel-titanium shape memory film having no less than about 51.5 atomic percent nickel, the vacuum deposition occurring under at least one vacuum deposition process condition selected from at least one of chamber pressure, deposition pressure, and partial pressure of a process gas, said at least one process condition optimized to minimize formation of inter- and intra-granular precipitates in the bulk material of the nickel-titanium crystalline film; and b. removing the deposited generally tubular, crystalline nickel-titanium shape memory film from the generally cylindrical substrate.
 15. The method according to claim 14, wherein the deposited generally tubular film of nickel-titanium has a composition of between about 51.5 and about 55.0 atomic percent nickel.
 16. The method according to claim 14, wherein during the deposition of the nickel and titanium, the substrate is rotated, and wherein the process condition controlled is a deposition rate and the deposition rate is no less than about 20 nm/sec.
 17. The method according to claim 14, wherein a source of the nickel and the titanium to be deposited is a nickel-titanium alloy.
 18. The method according to claim 14, wherein a source of the nickel and the titanium to be deposited is a binary nickel-titanium alloy.
 19. The method according to claim 14, further comprising, prior to step (a), a step of imparting a pattern defining the first and second structural elements onto the exterior surface of the substrate, and wherein the pattern is transferred to the tubular film of nickel-titanium during step (a).
 20. The method according to claim 14, further comprising a step of imparting a pattern defining the first and second structural elements onto the tubular film of nickel-titanium after step (a). 